EP0696445A1 - Endosseous implant system - Google Patents
Endosseous implant system Download PDFInfo
- Publication number
- EP0696445A1 EP0696445A1 EP95302105A EP95302105A EP0696445A1 EP 0696445 A1 EP0696445 A1 EP 0696445A1 EP 95302105 A EP95302105 A EP 95302105A EP 95302105 A EP95302105 A EP 95302105A EP 0696445 A1 EP0696445 A1 EP 0696445A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- moiety
- coronal
- section
- implant body
- tension
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Ceased
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
- A61C8/0022—Self-screwing
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0001—Impression means for implants, e.g. impression coping
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
- A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
- A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
- A61C8/0066—Connecting devices for joining an upper structure with an implant member, e.g. spacers with positioning means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
- A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
- A61C8/0069—Connecting devices for joining an upper structure with an implant member, e.g. spacers tapered or conical connection
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
- A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
- A61C8/0069—Connecting devices for joining an upper structure with an implant member, e.g. spacers tapered or conical connection
- A61C8/0071—Connecting devices for joining an upper structure with an implant member, e.g. spacers tapered or conical connection with a self-locking taper, e.g. morse taper
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0086—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools with shock absorbing means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0087—Means for sterile storage or manipulation of dental implants
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0089—Implanting tools or instruments
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0048—Connecting the upper structure to the implant, e.g. bridging bars
- A61C8/005—Connecting devices for joining an upper structure with an implant member, e.g. spacers
- A61C8/006—Connecting devices for joining an upper structure with an implant member, e.g. spacers with polygonal positional means, e.g. hexagonal or octagonal
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30721—Accessories
- A61F2/30749—Fixation appliances for connecting prostheses to the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30108—Shapes
- A61F2002/30199—Three-dimensional shapes
- A61F2002/30205—Three-dimensional shapes conical
- A61F2002/3021—Three-dimensional shapes conical frustoconical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30329—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2002/30405—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements made by screwing complementary threads machined on the parts themselves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
- A61F2002/30836—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves knurled
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
- A61F2002/3085—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves with a threaded, e.g. self-tapping, bone-engaging surface, e.g. external surface
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0067—Three-dimensional shapes conical
Definitions
- This invention relates generally to artificial orthopedic implant prostheses, and particularly, but not exclusively, to dental implant prostheses.
- an orthopedic prosthesis whether it be a dental prosthesis such as bridge work or other bone implant prosthesis such as an artificial limb, requires affixing the prosthesis to one of the patient's bones. Generally, this is accomplished by first affixing a metallic implant connection member into the connector bone and then affixing the prosthesis to the implant connection member.
- a fundamental problem with the installation of orthopedic prostheses is the tendency of the bone installation sight to "wear out” over time. This resorption of bone (“wear out”) is characteristically seen after load is introduced. Clinical evidence of this destruction begins at the coronal aspect and moves progressively towards the apical end of the fixture creating a uniform saucerization.
- the fundamental problem is the inability of prior art implant systems to evenly distribute occlusal loads along the length of the implant connection member. This results in uneven stress to the bone immediately surrounding the implant connection member, and leads to eventual break-down of the implant sight. This problem is particularly acute with respect to dental implants, but it is also a common problem with respect to other orthopedic implants.
- an endosseous implant system wherein the implant member is capable of more evenly distributing occlusal loads along the entire length of the implant connection member.
- the invention satisfies this need.
- the invention is an endosseous implant body for implantation into bone.
- the implant body has a coronal end, a distal end and a plurality of segments proximate to the coronal end.
- Each segment has a circular cross-section perpendicular to the longitudinal axis of the implant body and comprises a frustro-conical compression moiety and a frustro-conical tension moiety.
- tension moiety means the coronal-side portion of the segment whose surface area generally faces in the direction of the coronal end of the implant body.
- compression moiety means the distal-side portion of the segment whose surface area generally faces towards the distal end of the implant body.
- both the compression moiety and the tension moiety have a maximum diameter, a minimum diameter and a substantially flat surface area disposed therebetween at an angle of incidence with respect to the longitudinal axis of the implant body.
- the angle of incidence is the obtuse angle formed by the intersection of the longitudinal axis of the implant body and a line drawn tangent to the flat surface area of one of the moieties.
- the compression moiety is joined "back-to-back" with the tension moiety along each moiety's respective maximum diameter.
- the minimum diameter of each compression moiety is identical to and is attached to the minimum diameter of a tension moiety of an adjacent segment, if any.
- angles of incidence of all segment moieties and the surface areas of all segment moieties are chosen so that, when the implant body is implanted into bone and a lateral force is applied to the coronal end of the body, that portion of the lateral force which is exerted by the compression moiety of each segment against the surrounding bone is greater than that portion of the lateral force which is exerted by the compression moiety of an adjacent segment disposed more proximate to the coronal end.
- each of the tension moieties are chosen so that, when the body is implanted into bone and a lateral force is applied to the coronal end of the body, that portion of the lateral force which is exerted by the tension moiety of each segment against the surrounding bone is less than that portion of the lateral force which is exerted by the tension moiety of an adjacent segment disposed more proximate to the coronal end.
- each compression moiety surface is greater than the width of the compression moiety surface of an adjacent segment disposed more proximate to the distal end.
- the width of each tension moiety surface is generally chosen so as to be greater than the width of the tension moiety surface of an adjacent segment disposed more proximate to the coronal end.
- each compression moiety surface can be chosen so as to be greater than the angle of incidence of the compression moiety surface of the compression moiety disposed more proximate to the distal end.
- the angle of incidence of each compression moiety surface is generally chosen so that the angle of incidence of any one compression moiety surface is greater than the angle of incidence of the compression moiety surface disposed more proximate to the coronal end.
- the invention is also a combination of an implant body having a coronal end bore and a plug disposed within the coronal end bore.
- the plug has a coronal end adapted for attachment to a prosthesis attachment member.
- the coronal end of the plug has at least one non-circular cross-section so that it attaches to the prosthesis attachment member in one and only one position.
- the plug may also be in the form of a tapered external hex or spline or slot.
- the invention is also an implant delivery system comprising the combination described immediately above and an implanting tool.
- Such an implant system can be conveniently used to install the implant combination described above.
- FIG. 1 illustrates a typical prior art endosseous dental implant body 1 and prosthesis 2 implanted into a patient's jaw bone 3 below the gum line 4 .
- a lateral force 5 is applied to such a typical dental implant 1 , that lateral force 5 tends to rotate the implant 1 about a certain point in the implant 1 , which will be referred to herein as the "centroid 6 .”
- the location of the centroid 6 depends on the design of the implant 1 .
- the lateral force 5 generates stress forces f i within the jawbone 3 as illustrated by the force diagram shown in FIG. 2. As can be seen from FIG.
- the stress force diagram illustrated in FIG. 2 arises typically from an implant body 1 having a substantially cylindrical shape with "straight" sidewalls 7 . Because the sidewalls 7 are "straight,” and generally vertical with respect to the lateral force 5 applied to the prosthesis 2 , the resultant stress forces f i applied to adjacent bone 3 at any particular location along the length of one side 7 of the implant body 1 differ only from the stress forces f i applied to bone at another location by the distance between the location and the centroid 6 of the implant body 1 . Thus, a force diagram similar to FIG. 2 will always result from lateral forces 5 applied to implant bodies 1 having "straight" sides 7 .
- the implant body 10 of FIG. 14 does not have "straight" sides. Rather the sides 14 have surfaces 16 of two different types: (1) surfaces which generally face the coronal end 18 of the implant body 10 , and (2) surfaces which generally face the distal end 20 of the implant body 10 . It can be mathematically shown that the surfaces facing the coronal end 18 of the implant body 10 (which shall herein be referred to as “tension surfaces 22 ”) generally exert less stress on bone 3 adjacent to the implant body 10 than do surfaces generally facing perpendicular to the implant body 10 (as in prior art implant bodies with "straight sides”).
- compression surfaces 24 generally exert greater stress on bone 3 adjacent to the impact body 10 than do surfaces generally facing perpendicular to the implant body 10 .
- compression surfaces 24 the surfaces facing the base of the implant body
- the surface having the greater surface area and/or the surface having the greatest "angle of incidence 26 " will exert the greater stress on bone 3 adjacent to the implant body 10 .
- the "angle of incidence 26 " is herein defined as the obtuse angle resulting from the intersection of the longitudinal axis 28 of the implant body 10 and a line 30 disposed tangent to the particular surface 16 in question.
- FIG. 4 illustrates an implant body having two tension surfaces (t1 and t2, respectively) and two compression surfaces (c1 and c2, respectively).
- the angle of incidence of tension surface t1 is x1, and the angle of incidence of tension surface t2 is x2.
- the angle of incidence of compression surface c1 is y1 and the angle of incidence of compression surface c2 is y2.
- the inventor has constructed an implant body 10 which substantially evenly distributes lateral stresses 5 placed upon the impact body 10 (such as illustrated in FIG. 3).
- the inventor has accomplished this by providing an implant body 10 having alternating tension surfaces 22 and compression surfaces 24 .
- the surface areas and angles of incidence 26 of the tension surfaces 22 are chosen so that the portion of a lateral force 5 exerted by each of the tension surfaces increases from the centroid to the coronal end of the implant body.
- the surface areas and angles of incidence of the compression surfaces 24 are chosen so that the portion of a lateral force 5 exerted by each of the compression surfaces 24 decreases from the centroid of the implant body to the coronal end of the implant body.
- FIGS. 5-7 A typical embodiment of the implant body 10 of the present invention is illustrated in FIGS. 5-7.
- the implant body 10 has a coronal end 18 , a distal end 20 , a longitudinal axis 28 , and a plurality of segments 34 proximate to the coronal end 18 .
- Each segment 34 has a circular cross-section perpendicular to the longitudinal axis 28 and comprises a frustro-conical tension moiety 36 and a frustro-conical compression moiety 38 .
- Both moieties 36 and 38 have a maximum diameter 40 , a minimum diameter 42 , and a substantially flat surface area 16 disposed therebetween. Each such surface 16 is disposed at an angle of incidence 26 with respect to the longitudinal axis 28 .
- the maximum diameter 40 of the compression moiety 38 in each segment 34 is the same as the maximum diameter 40 of the tension moiety 36 in that segment 34 .
- each compression moiety 38 is joined to a tension moiety 36 along each moiety's respective maximum diameter 40 .
- the minimum diameter 42 of each compression moiety 38 is identical to and is attached to the minimum diameter 42 of a tension moiety 36 of an adjacent segment 34 .
- angles of incidence 26 and the surface areas of the compression moieties 38 are chosen so that, when the implant body 10 is implanted into bone 3 and a lateral force 5 is applied to the coronal end 18 of the implant body 10 , that portion of the lateral force 5 which is exerted by the compression moiety 38 of each segment 34 against the surrounding bone 3 is greater than that portion of the lateral force 5 which is exerted by the compression moiety 38 of an adjacent segment 34 disposed more proximate to the coronal end 18 .
- angles of incidence 26 and the surface areas of the tension moieties 36 are chosen so that, when the implant body 10 is implanted into bone 3 and a lateral force 5 is applied to the coronal end 18 of the implant body 10 , that portion of the lateral force 5 which is exerted by the tension moiety 36 of each segment 34 against the surrounding bone 3 is less than that portion of the lateral force 5 which is exerted by the tension moiety 36 of an adjacent segment 34 disposed more proximate to the coronal end 18 .
- the vertical width 44 of each individual segment 34 is generally held constant and the width of each compression moiety surface 16 is made greater than the width of the compression moiety surface 16 of an adjacent segment 34 disposed more proximate to the distal end 20 .
- the width of each tension moiety surface 16 is made greater than the width of the tension moiety surface 16 of an adjacent segment 34 disposed more proximate to the coronal end 18 .
- each segment 34 is held generally constant and the angle of incidence 26 of each compression moiety surface 16 is greater than the angle of incidence 26 of the compression moiety 38 of an adjacent segment 34 disposed more proximate to the distal end 20 .
- the angle of incidence 26 of each tension moiety surface 16 is greater than the angle of incidence 26 of the tension moiety surface 16 of an adjacent segment 34 disposed more proximate to the coronal end 18 .
- any combination of angles of incidence 26 and surface areas can be combined in a series of segments 34 so long as, when the implant body 10 is implanted into bone 3 and a lateral force 5 is applied to the coronal end 18 of the implant body 10 , (1) that portion of the lateral force 5 which is exerted by the compression moiety 38 of each segment 34 against the surrounding bone 3 is greater than the portion of the lateral force 5 which is exerted by the compression moiety 38 of an adjacent segment 34 disposed more proximate to the coronal end 18 and (2) that portion of the lateral force 5 which is exerted by the tension moiety 36 of each segment 34 against the surrounding bone 3 is less than that portion of the lateral force 5 which is exerted by the tension moiety 36 of an adjacent segment 34 disposed more proximate to the coronal end 18 .
- the segments 34 can be discrete, as illustrated in the drawings. Alternatively, the segments 34 can be disposed in one continuous helix.
- the implant body 10 is made from one of the many corrosion resistant metal alloys known in the art.
- the overall length of the implant body 10 is typically between about 8 millimeters and about 18 millimeters.
- FIG. 8 illustrated three different sizes of implant bodies 10 .
- a typical dental implant body of the invention 10 has four segments 34 .
- the distance between the minimum diameter 42 of the compression segment 38 nearest the coronal end 18 of the implant body 10 and the minimum diameter 42 of the tension moiety 36 most distal to the coronal end 18 of the implant body 10 is typically between about 4 and about 8 millimeters. Implant bodies 10 having additional segments 34 are, of course, possible.
- the coronal end 18 of the implant body 10 defines a tapered coronal bore 44 having circular cross-sections perpendicular to the longitudinal axis 28 of the implant body 10 .
- the coronal bore 44 comprises a tapered distal section 46 and a coronal section 48 .
- the coronal section 48 has a substantially circular cross-section which is greater than the maximum cross-section of the distal section 46 .
- the fact that the coronal section 48 has greater cross-section than the distal section 46 is important in that it allows for the attachment of a prosthesis attachment structure to be "countersunk" into the implant body 10 , below the level of the bone crest.
- the distal end 20 of the implant body 10 is slightly tapered towards the distal end 20 . Such tapering facilitates the firm installation of the implant body 10 into an implant site.
- the distal end 20 of the implant body 10 can be externally threaded with self-tapping threads 50 as illustrated in FIG. 7.
- a pair of grooves 52 disposed 180° apart, are defined within the exterior surface of the distal end 20 .
- the grooves 52 provide space for bone chips to gather when the implant body 10 is threaded into the implant site.
- the distal end 20 of the implant body 10 is knurled as illustrated in FIG. 8.
- the distal end 20 of the implant body 10 is knurled and the knurling 54 has a cross-cut diamond shape, such as illustrated in FIG. 8.
- Such knurling 54 creates its own bone chips at the time of insertion which further assist in redistributing stresses placed on the implant body 10 .
- the implant body 10 is preferably used in conjunction with an anti-rotational plug 56 such as illustrated in FIGS. 9-12.
- the plug 56 acts as a host for all coronal attachments.
- the plug 56 has a distal moiety 58 , a coronal moiety 60 , and a longitudinal axis 62 .
- the distal moiety 58 is sized and dimensioned to match the coronal bore 44 of the implant body 10 so that the plug 56 can be firmly affixed therein.
- the plug 56 may also be designed with parallel walls as shown in FIG. 9A to assure parallelism between the longitudinal axis 26 of the implant body 10 and the longitudinal axis of the plug 56 during assembly. In this case, a Mores taper would preferably be defined in the attachment structure (described below).
- the coronal moiety 60 of the plug 56 would be machined most preferably at a 2° Mores taper to assure accuracy and stability.
- the coronal moiety 60 has a maximum cross-section perpendicular to the longitudinal axis 62 of the plug 56 which is smaller than the maximum cross-section of the distal moiety 58 perpendicular to the longitudinal axis 62 of the plug 56 .
- FIG. 13 which illustrates a typical plug 56 disposed within an implant 10
- the fact that the corona moiety 60 of the plug 56 has a smaller cross-section than the distal moiety 58 results in an annular gap 64 between the inner surface 66 of the coronal bore 44 within the implant body 10 and the coronal moiety 60 of the plug 56 .
- this annular gap 64 facilitates the "countersinking" of the prosthesis attachment structure (described below) to the implant body-plug combination 67 .
- the tapered segment which creates the annular gap 64 may be defined in the prosthesis attachment structure in both the plug 56 and the prosthesis attachment structure to create an intimate fit upon proper seating.
- the coronal moiety 60 of the plug 56 has at least one cross-section perpendicular to the longitudinal axis 62 of the plug which is non-circular. As will be seen below, this important feature allows for the reinstallation of an attachment structure (which has been previously removed from the coronal moiety 60 of the plug 56 ) to precisely the original location.
- the non-circular cross-section of the coronal moiety 60 can take on any of a wide variety of shapes. As shown in FIG. 10, the coronal moiety 60 of the plug 56 has a single cam projection 68 . In the embodiment illustrated in FIG. 12, the coronal moiety 60 of the plug 56 has a hexagonal cross-section. Key-ways, locking splines, slots, flats and other cross-sectional shapes can also be used.
- the coronal moiety 60 has an internally threaded plug bore 70 disposed along the longitudinal axis 62 of the plug 56 .
- This threaded plug bore 70 facilitates the installation of a prosthesis 12 or other attachments to the plug 56 by providing an attachment site for an attachment screw.
- the coronal moiety 60 be slightly tapered. It is most preferred that such tapering be a Mores taper 71 of between about 1° and about 2°, ideally, 1°, 30'. Such taper facilitates the installation of an attachment structure to the coronal moiety 60 .
- the plug 56 is disposed within the implant body 10 as illustrated in FIGS. 13-14.
- the plug 56 can be welded within the implant body 10 , cemented, or attached by any other suitable means.
- the distal end 58 of the plug 56 is slightly typically tapered as is the distal section 46 of the coronal bore 44 within the implant body 10 . Such matched tapering facilitates the installation of the plug 56 within the implant body 10 . Alternatively, the plug 56 is not tapered. This shape may be preferred to assure proper orientation of the plug 56 prior to welding within the implant body 10 .
- FIGS. 15-17 illustrate a typical healing cap 72 useful in the invention.
- the healing cap 72 can be used to seal the coronal end 74 of the tapered implant body-plug combination 67 after the combination 67 has been implanted into a patient (as illustrated in FIGS. 18 and 19).
- the healing cap 72 has a cap portion 78 sized and dimensioned to match up with the coronal end 18 of the implant body 10 .
- the healing cap 72 also has a threaded distal end 80 sized and dimensioned to thread into the internally threaded plug bore 70 of the plug 56 .
- the cap portion 78 has a coronal bore 82 with a non-circular cross-section. This bore 82 is adapted to accept a torquing tool which can be used to thread the healing cap 72 into the coronal moiety 60 of the plug 56 .
- FIGS. 20-21 illustrate a typical attachment structure 84 useful for attaching impression attachments, prostheses or other attachments to the implant body-plug combination 67 .
- the attachment structure 84 comprises an elongated hollow section 86 having a coronal moiety 88 with an open coronal end 90 , a distal moiety 92 with an open distal end 94 and a longitudinal axis 96 .
- the distal end 92 of the attachment structure 84 is shaped and dimensioned to receive and engage the non-circular cross-section of the coronal moiety 60 of the plug 56 .
- the distal end 94 of the attachment structure 84 is shaped to receive the coronal end 60 of a plug 56 having a cam projection 68 , such as illustrated in FIG. 9.
- this feature allows the practitioner to remove the attachment structure 84 from the plug 56 and thereafter reinstall the attachment structure 84 onto the plug 56 in precisely the same alignment in which it was initially installed.
- one or both components may also be machined parallel and alone be tapered to achieve the same results.
- the coronal moiety 88 is preferably detachable from the distal moiety 92 .
- the attachment structure 84 can be affixed to the plug 56 by an elongated first screw 98 which is disposed within the hollow section 86 of the attachment structure 84 .
- a first screw 98 is illustrated in FIGS. 22 and 23.
- the threads of the first screw 98 are chosen to match the internal threads in the bore 70 of the plug 56 .
- FIG. 24 illustrates the first screw 98 disposed within the attachment structure 84 .
- the first screw 98 has a coronal bore 99 with a non-circular cross-section. This bore 99 is adapted to accept a torquing tool which can be used to thread the first screw 98 into the coronal moiety 60 of the plug 56 .
- the distal moiety 92 of the attachment structure 84 has a first external surface section 100 immediately proximate to the distal end 94 of the attachment structure 84 and a second external surface section 102 immediately proximate to the first external surface section 100 .
- the cross-sections of the first and second external surface sections 100 and 102 are sized and dimensioned to match the cross-section of the external surface of the implant body 10 immediately proximate to the coronal end 18 of the implant body 10 .
- the width 103 of the first external surface section 100 is substantially the same as the depth 104 of the coronal section 48 of the implant body coronal bore 44 . As shown in FIG.
- this design allows the first external surface section 100 to nest within the coronal section 48 of the coronal bore 44 of the implant body 10 .
- the diameter of the second external surface section 102 is substantially the same as the diameter of the external surface of the implant body 10 immediately proximate to its coronal end 18 . As illustrated in FIG. 25, this provides for a smooth transitional surface between the impact body 1 0 and the attachment structure 84 .
- FIGS. 25-27 illustrate the attachment structure 84 as it is combined with the implant body 10 and the plug 56 , using the first screw 98 .
- FIG. 28 illustrates the combination illustrated in FIG. 25 in further combination with a dental prosthesis 12 attached to the attachment structure 84 .
- FIGS. 31-33 Such a sheath 106 is illustrated in FIGS. 31-33.
- the sheath 106 can be made of a plastic material. Other suitable materials can, of course, be used, i.e., T i , T i 6-4 alloy or T i 13-13, etc.
- the sheath 106 has an open coronal end 108 and an open distal end 110 .
- the coronal end 108 is sized and dimensioned to cover the coronal end 90 of the attachment structure 84 .
- the opening 112 in the corona end 108 of the sheath 106 is sized and dimensioned to receive a second screw 114 as illustrated in FIGS. 34 and 35.
- the second screw 114 is threaded in such a way that it can be attached within the bore 70 of the plug 56 .
- the second screw 114 has a shoulder 116 sized and dimensioned to firmly retain the attachment structure 84 to the plug 56 .
- the second screw 114 also has a head 118 sized and dimensioned to firmly attach the sheath 106 to the attachment structure 84 .
- the second screw 114 has a coronal bore 119 with a non-circular cross-section. This bore 119 is adapted to accept a torquing tool which can be used to thread the second screw 114 into the coronal moiety 60 of the plug 56 .
- the implant body-plug combination 76 can be conveniently packaged with an implant tool 120 within a protective cover 122 so that the practitioner can quickly and easily install the implant body-plug combination 76 by merely removing the cover 122 and using the installation tool 120 to install the implant body 10 within a pre-prepared implant site.
- a typical implant tool 120 is illustrated in FIGS. 37-44.
- the tool 120 comprises a shank portion 124 which is attachable to a removable handle portion 126 .
- the distal end 128 of the shank portion 124 is sized and dimensioned to match up and engage the coronal moiety 60 of the plug 56 and the coronal end 18 of the implant body 10 .
- the distal end 128 of the shank 124 is sized and dimensioned to accept the removable handle portion 126 .
- Both the handle portion 126 and the shank 124 are hollow so that a third screw 130 can be used to firmly attach the handle portion 126 to the shank 124 and the shank 124 to the plug 56 as illustrated in FIG. 36.
- the third screw 130 has a coronal bore 131 with a non-circular cross-section. This bore 131 is adapted to accept a torquing tool which can be used to thread the third screw 130 into the coronal moiety 60 of the plug 56 .
- the implant body of the invention 10 is installed into an implant site which has been previously prepared in the bone 3 of the patient.
- Such an implant site can be prepared using tapered drills such as those illustrated in FIGS. 45-50.
- the drill illustrated in FIG. 45 is a typical pilot drill 132 .
- the drill illustrated in FIG. 48 is a larger drill 134 for use after a pilot hole is drilled (by the pilot 132 drill) to prepare the full dimension of the implant site.
Landscapes
- Health & Medical Sciences (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Dentistry (AREA)
- Epidemiology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Abstract
Description
- This invention relates generally to artificial orthopedic implant prostheses, and particularly, but not exclusively, to dental implant prostheses.
- The installation of an orthopedic prosthesis, whether it be a dental prosthesis such as bridge work or other bone implant prosthesis such as an artificial limb, requires affixing the prosthesis to one of the patient's bones. Generally, this is accomplished by first affixing a metallic implant connection member into the connector bone and then affixing the prosthesis to the implant connection member.
- A fundamental problem with the installation of orthopedic prostheses is the tendency of the bone installation sight to "wear out" over time. This resorption of bone ("wear out") is characteristically seen after load is introduced. Clinical evidence of this destruction begins at the coronal aspect and moves progressively towards the apical end of the fixture creating a uniform saucerization. The fundamental problem is the inability of prior art implant systems to evenly distribute occlusal loads along the length of the implant connection member. This results in uneven stress to the bone immediately surrounding the implant connection member, and leads to eventual break-down of the implant sight. This problem is particularly acute with respect to dental implants, but it is also a common problem with respect to other orthopedic implants.
- Therefore, there is a need for an endosseous implant system wherein the implant member is capable of more evenly distributing occlusal loads along the entire length of the implant connection member.
- The invention satisfies this need. The invention is an endosseous implant body for implantation into bone. The implant body has a coronal end, a distal end and a plurality of segments proximate to the coronal end.
- Each segment has a circular cross-section perpendicular to the longitudinal axis of the implant body and comprises a frustro-conical compression moiety and a frustro-conical tension moiety. As used herein, the term "tension moiety" means the coronal-side portion of the segment whose surface area generally faces in the direction of the coronal end of the implant body. Conversely, the term "compression moiety" as used herein means the distal-side portion of the segment whose surface area generally faces towards the distal end of the implant body.
- Within each segment, both the compression moiety and the tension moiety have a maximum diameter, a minimum diameter and a substantially flat surface area disposed therebetween at an angle of incidence with respect to the longitudinal axis of the implant body. The angle of incidence is the obtuse angle formed by the intersection of the longitudinal axis of the implant body and a line drawn tangent to the flat surface area of one of the moieties.
- The compression moiety is joined "back-to-back" with the tension moiety along each moiety's respective maximum diameter. The minimum diameter of each compression moiety is identical to and is attached to the minimum diameter of a tension moiety of an adjacent segment, if any.
- The angles of incidence of all segment moieties and the surface areas of all segment moieties are chosen so that, when the implant body is implanted into bone and a lateral force is applied to the coronal end of the body, that portion of the lateral force which is exerted by the compression moiety of each segment against the surrounding bone is greater than that portion of the lateral force which is exerted by the compression moiety of an adjacent segment disposed more proximate to the coronal end.
- Likewise, the angles of incidence and the surface areas of each of the tension moieties are chosen so that, when the body is implanted into bone and a lateral force is applied to the coronal end of the body, that portion of the lateral force which is exerted by the tension moiety of each segment against the surrounding bone is less than that portion of the lateral force which is exerted by the tension moiety of an adjacent segment disposed more proximate to the coronal end.
- In one embodiment, the width of each compression moiety surface is greater than the width of the compression moiety surface of an adjacent segment disposed more proximate to the distal end. In this embodiment, the width of each tension moiety surface is generally chosen so as to be greater than the width of the tension moiety surface of an adjacent segment disposed more proximate to the coronal end.
- Alternatively, the angle of incidence of each compression moiety surface can be chosen so as to be greater than the angle of incidence of the compression moiety surface of the compression moiety disposed more proximate to the distal end. In this embodiment, the angle of incidence of each compression moiety surface is generally chosen so that the angle of incidence of any one compression moiety surface is greater than the angle of incidence of the compression moiety surface disposed more proximate to the coronal end.
- The invention is also a combination of an implant body having a coronal end bore and a plug disposed within the coronal end bore. The plug has a coronal end adapted for attachment to a prosthesis attachment member. The coronal end of the plug has at least one non-circular cross-section so that it attaches to the prosthesis attachment member in one and only one position. The plug may also be in the form of a tapered external hex or spline or slot.
- The invention is also an implant delivery system comprising the combination described immediately above and an implanting tool. Such an implant system can be conveniently used to install the implant combination described above.
- These and other features, aspects and advantages of the present invention will become better understood with reference to the following description, appended claims and accompanying drawings where:
- FIGURE 1 is a diagrammatic representation of a lateral force exerted on an endosseous prosthesis implanted into bone;
- FIGURE 2 is a force diagram showing typical forces imposed upon the endosseous implant of FIG. 1;
- FIGURE 3 is a force diagram showing ideal forces imposed upon the endosseous implant of FIG. 1;
- FIGURE 4 is a diagrammatic representation of a lateral force exerted on an endosseous prosthesis having features of the invention implanted into bone;
- FIGURE 5 is a side view of an implant body having features of the invention;
- FIGURE 6 is the coronal end view of the implant body shown in FIG. 5;
- FIGURE 7 is the distal end view of the implant body of FIG. 5:
- FIGURE 8 is a side view of three implant bodies having features of the invention, including knurled distal ends;
- FIGURE 9 is a side view in partial cross-section of a plug having features of the invention;
- FIGURE 9A is a side view in partial cross-section of an alternative plug which is non-tapered;
- FIGURE 10 is a coronal view of the plug of FIG. 9;
- FIGURE 11 is a second embodiment of a plug having features of the invention;
- FIGURE 12 is a coronal view of the plug of FIG. 11 with the external tapered hex design option;
- FIGURE 13 is a side view in partial cross-section of an implant combination having features of the invention;
- FIGURE 14 is a coronal view of the combination shown in FIG. 13;
- FIGURE 15 is a side view in partial cross-section of a healing cap useful in the invention;
- FIGURE 16 is a distal end view of the healing cap of FIG. 15;
- FIGURE 17 is a coronal end view of the healing cap of FIG. 15;
- FIGURE 18 is a side view in partial cross-section of the combination of an implant body-plug and healing cap having features of the invention;
- FIGURE 19 is a coronal end view of the combination of FIG. 18;
- FIGURE 20 is a side view in partial cross-section of an attachment structure having features of the invention;
- FIGURE 21 is a distal end view of the attachment structure of FIG. 20;
- FIGURE 22 is a side view in partial cross-section of a screw useful in the attachment of the attachment structure of FIG. 20;
- FIGURE 23 is a coronal end view of the screw illustrated in FIG. 22;
- FIGURE 24 is a side view in partial cross-section of a combination of the attachment structure of FIG. 20 and the screw of FIG. 22.
- FIGURE 25 is a side view in partial cross-section of another implant combination having features of the invention;
- FIGURE 26 is a coronal end view of the combination of FIG. 20;
- FIGURE 27 is a distal end view of the combination of FIG. 20;
- FIGURE 28 is a side view in partial cross-section of a further combination having features of the invention;
- FIGURE 29 is a side view in partial cross-section of a combination having features of the invention, including a cover sheath;
- FIGURE 30 is a coronal end of the combination of FIG. 29;
- FIGURE 31 is a side view in partial cross-section of a sheath useable in the combination of FIG. 29;
- FIGURE 32 is a coronal end view of the sheath of FIG. 31;
- FIGURE 33 is a distal end view of the sheath of FIG. 31;
- FIGURE 34 is a side view in partial cross-section of a screw useful in the combination of FIG. 29;
- FIGURE 35 is a coronal end view of the screw of FIG. 34;
- FIGURE 36 is a side view in partial cross-section of an endosseous implant delivery system having features of the invention;
- FIGURE 37 is a side view in partial cross-section of a screw useful in the delivery system of FIG. 36;
- FIGURE 38 is a coronal end view of the screw of FIG. 37;
- FIGURE 39 is a side view in partial cross-section of a tool shank useful in the delivery system of FIG. 36;
- FIGURE 40 is a distal end view of the tool shank of FIG. 39;
- FIGURE 41 is a coronal end view of the shank of FIG. 39;
- FIGURE 42 is a tool handle useful in the delivery system of FIG. 36;
- FIGURE 43 is a distal end view of the handle of FIG. 42;
- FIGURE 44 is a coronal end view of the handle of FIG. 42;
- FIGURE 45 is a side view in partial cross-section of a pilot drill useful in the invention;
- FIGURE 46 is a coronal end view of the pilot drill of FIG. 45;
- FIGURE 47 is a distal end view of the pilot drill of FIG. 45;
- FIGURE 48 is a side view in partial cross-section of a drill useful in the invention as the final sizing drill prior to insertion;
- FIGURE 49 is a coronal end view of the drill of FIG. 48; and
- FIGURE 50 is a distal end view of the drill of FIG. 48.
- The invention will be described by using specific language with reference to the accompanying illustrated embodiments. Although much of this description is directed to dental implants, it is understood that the scope of the invention includes other orthopedic implants and any modifications or alterations which would be obvious to those skilled in the art.
- FIG. 1 illustrates a typical prior art endosseous dental implant body 1 and
prosthesis 2 implanted into a patient'sjaw bone 3 below thegum line 4. When a lateral force 5 is applied to such a typical dental implant 1, that lateral force 5 tends to rotate the implant 1 about a certain point in the implant 1, which will be referred to herein as the "centroid 6." The location of thecentroid 6 depends on the design of the implant 1. The lateral force 5 generates stress forces fi within thejawbone 3 as illustrated by the force diagram shown in FIG. 2. As can be seen from FIG. 2, with prior art implant bodies the stress forces fi placed upon theadjacent bone 3 furthest from thecentroid 6 are much greater than the stress forces placed upon thebone 3 near thecentroid 6. The excessive stress forces fi placed upon thebone 3 adjacent to the implant body 1 furthest from thecentroid 6 frequently results in degradation of thatbone 3 over time. - What would be ideal would be an endosseous implant body which, when a lateral force is applied to the implant body, would evenly distribute the stress forces fi applied to the bone adjacent to the implant body. Such an ideal stress force distribution is illustrated in FIG. 3. It is the principal object of the present invention to provide an endosseous implant body which will more closely approximate the stress forces illustrated in FIG. 3 (rather than the stress forces associated with prior art implants, as illustrated in FIG. 2).
- The stress force diagram illustrated in FIG. 2 arises typically from an implant body 1 having a substantially cylindrical shape with "straight" sidewalls 7. Because the sidewalls 7 are "straight," and generally vertical with respect to the lateral force5 applied to the
prosthesis 2, the resultant stress forces fi applied toadjacent bone 3 at any particular location along the length of one side 7 of the implant body 1 differ only from the stress forces fi applied to bone at another location by the distance between the location and thecentroid 6 of the implant body 1. Thus, a force diagram similar to FIG. 2 will always result from lateral forces 5 applied to implant bodies 1 having "straight" sides 7. - Consider now the
endosseous implant body 10 andprosthesis 12 illustrated in FIG. 4. Note that theimplant body 10 of FIG. 14 does not have "straight" sides. Rather thesides 14 havesurfaces 16 of two different types: (1) surfaces which generally face thecoronal end 18 of theimplant body 10, and (2) surfaces which generally face thedistal end 20 of theimplant body 10. It can be mathematically shown that the surfaces facing thecoronal end 18 of the implant body 10 (which shall herein be referred to as "tension surfaces 22") generally exert less stress onbone 3 adjacent to theimplant body 10 than do surfaces generally facing perpendicular to the implant body 10 (as in prior art implant bodies with "straight sides"). Also, it can be mathematically shown that the surfaces facing the base of the implant body (herein referred to as "compression surfaces 24") generally exert greater stress onbone 3 adjacent to theimpact body 10 than do surfaces generally facing perpendicular to theimplant body 10. Still further, it can be mathematically shown that between any two otherwise identical tension surfaces 22 or any two otherwise identical compression surfaces 24, the surface having the greater surface area and/or the surface having the greatest "angle ofincidence 26" will exert the greater stress onbone 3 adjacent to theimplant body 10. As illustrated in FIG. 4, the "angle ofincidence 26" is herein defined as the obtuse angle resulting from the intersection of thelongitudinal axis 28 of theimplant body 10 and aline 30 disposed tangent to theparticular surface 16 in question. FIG. 4 illustrates an implant body having two tension surfaces (t₁ and t₂, respectively) and two compression surfaces (c₁ and c₂, respectively). The angle of incidence of tension surface t₁ is x₁, and the angle of incidence of tension surface t₂ is x₂. Similarly, the angle of incidence of compression surface c₁ is y₁ and the angle of incidence of compression surface c₂ is y₂. - Based upon these properties of tension surfaces 22 and compression surfaces 24, the inventor has constructed an
implant body 10 which substantially evenly distributes lateral stresses 5 placed upon the impact body 10 (such as illustrated in FIG. 3). The inventor has accomplished this by providing animplant body 10 having alternating tension surfaces 22 and compression surfaces 24. The surface areas and angles ofincidence 26 of the tension surfaces 22 are chosen so that the portion of a lateral force 5 exerted by each of the tension surfaces increases from the centroid to the coronal end of the implant body. Conversely, the surface areas and angles of incidence of the compression surfaces 24 are chosen so that the portion of a lateral force 5 exerted by each of the compression surfaces 24 decreases from the centroid of the implant body to the coronal end of the implant body. Because the compression surfaces 24 exert more stress onadjacent bone 3 than do "straight surfaces," stress applied tobone 3 near thecentroid 32 of the implant body of theinvention 10 is greater than stress applied at thecentroid 6 of prior art implant bodies 1. Conversely, because tension surfaces 22 exert less stress onadjacent bone 3 than do "straight surfaces," the stress applied tobone 3 near thecoronal end 18 of the implant body of theinvention 10 is less than stress applied tobone 3 near the coronal end of a prior art implant body 1. Thus, the stress diagram associated with the implant body of the invention more closely approximates FIG. 3 than FIG. 2. - A typical embodiment of the
implant body 10 of the present invention is illustrated in FIGS. 5-7. Theimplant body 10 has acoronal end 18, adistal end 20, alongitudinal axis 28, and a plurality ofsegments 34 proximate to thecoronal end 18. - Each
segment 34 has a circular cross-section perpendicular to thelongitudinal axis 28 and comprises a frustro-conical tension moiety 36 and a frustro-conical compression moiety 38. Bothmoieties maximum diameter 40, aminimum diameter 42, and a substantiallyflat surface area 16 disposed therebetween. Eachsuch surface 16 is disposed at an angle ofincidence 26 with respect to thelongitudinal axis 28. Themaximum diameter 40 of thecompression moiety 38 in eachsegment 34 is the same as themaximum diameter 40 of thetension moiety 36 in thatsegment 34. As can be seen in FIG. 5, eachcompression moiety 38 is joined to atension moiety 36 along each moiety's respectivemaximum diameter 40. As can also be seen in FIG. 5, theminimum diameter 42 of eachcompression moiety 38 is identical to and is attached to theminimum diameter 42 of atension moiety 36 of anadjacent segment 34. - As noted above, the angles of
incidence 26 and the surface areas of thecompression moieties 38 are chosen so that, when theimplant body 10 is implanted intobone 3 and a lateral force 5 is applied to thecoronal end 18 of theimplant body 10, that portion of the lateral force 5 which is exerted by thecompression moiety 38 of eachsegment 34 against the surroundingbone 3 is greater than that portion of the lateral force 5 which is exerted by thecompression moiety 38 of anadjacent segment 34 disposed more proximate to thecoronal end 18. Also, the angles ofincidence 26 and the surface areas of thetension moieties 36 are chosen so that, when theimplant body 10 is implanted intobone 3 and a lateral force 5 is applied to thecoronal end 18 of theimplant body 10, that portion of the lateral force 5 which is exerted by thetension moiety 36 of eachsegment 34 against the surroundingbone 3 is less than that portion of the lateral force 5 which is exerted by thetension moiety 36 of anadjacent segment 34 disposed more proximate to thecoronal end 18. - In one typical embodiment of the
implant body 10 of the invention, thevertical width 44 of eachindividual segment 34 is generally held constant and the width of eachcompression moiety surface 16 is made greater than the width of thecompression moiety surface 16 of anadjacent segment 34 disposed more proximate to thedistal end 20. In this embodiment, it is common, although not necessary, that the width of eachtension moiety surface 16 is made greater than the width of thetension moiety surface 16 of anadjacent segment 34 disposed more proximate to thecoronal end 18. - In another typical embodiment of the
implant body 10 of the invention, thevertical width 44 of eachsegment 34 is held generally constant and the angle ofincidence 26 of eachcompression moiety surface 16 is greater than the angle ofincidence 26 of thecompression moiety 38 of anadjacent segment 34 disposed more proximate to thedistal end 20. In this embodiment, it is common, although not necessary, that the angle ofincidence 26 of eachtension moiety surface 16 is greater than the angle ofincidence 26 of thetension moiety surface 16 of anadjacent segment 34 disposed more proximate to thecoronal end 18. - One of ordinary skill in the art will immediately recognize that the typical embodiments described immediately above are not necessarily the only applications of the invention. Any combination of angles of
incidence 26 and surface areas can be combined in a series ofsegments 34 so long as, when theimplant body 10 is implanted intobone 3 and a lateral force 5 is applied to thecoronal end 18 of theimplant body 10, (1) that portion of the lateral force 5 which is exerted by thecompression moiety 38 of eachsegment 34 against the surroundingbone 3 is greater than the portion of the lateral force 5 which is exerted by thecompression moiety 38 of anadjacent segment 34 disposed more proximate to thecoronal end 18 and (2) that portion of the lateral force 5 which is exerted by thetension moiety 36 of eachsegment 34 against the surroundingbone 3 is less than that portion of the lateral force 5 which is exerted by thetension moiety 36 of anadjacent segment 34 disposed more proximate to thecoronal end 18. - The
segments 34 can be discrete, as illustrated in the drawings. Alternatively, thesegments 34 can be disposed in one continuous helix. - The
implant body 10 is made from one of the many corrosion resistant metal alloys known in the art. For dental implants, the overall length of theimplant body 10 is typically between about 8 millimeters and about 18 millimeters. FIG. 8 illustrated three different sizes ofimplant bodies 10. - A typical dental implant body of the
invention 10 has foursegments 34. The distance between theminimum diameter 42 of thecompression segment 38 nearest thecoronal end 18 of theimplant body 10 and theminimum diameter 42 of thetension moiety 36 most distal to thecoronal end 18 of theimplant body 10 is typically between about 4 and about 8 millimeters.Implant bodies 10 havingadditional segments 34 are, of course, possible. - As can be seen from FIGS. 5 and 6, the
coronal end 18 of theimplant body 10 defines a tapered coronal bore 44 having circular cross-sections perpendicular to thelongitudinal axis 28 of theimplant body 10. The coronal bore 44 comprises a tapereddistal section 46 and acoronal section 48. Thecoronal section 48 has a substantially circular cross-section which is greater than the maximum cross-section of thedistal section 46. As will be seen below, the fact that thecoronal section 48 has greater cross-section than thedistal section 46 is important in that it allows for the attachment of a prosthesis attachment structure to be "countersunk" into theimplant body 10, below the level of the bone crest. - In a typical embodiment, the
distal end 20 of theimplant body 10 is slightly tapered towards thedistal end 20. Such tapering facilitates the firm installation of theimplant body 10 into an implant site. - The
distal end 20 of theimplant body 10 can be externally threaded with self-tappingthreads 50 as illustrated in FIG. 7. In this embodiment, it is preferred that a pair ofgrooves 52, disposed 180° apart, are defined within the exterior surface of thedistal end 20. Thegrooves 52 provide space for bone chips to gather when theimplant body 10 is threaded into the implant site. - Preferably, the
distal end 20 of theimplant body 10 is knurled as illustrated in FIG. 8. Most preferably, thedistal end 20 of theimplant body 10 is knurled and theknurling 54 has a cross-cut diamond shape, such as illustrated in FIG. 8.Such knurling 54 creates its own bone chips at the time of insertion which further assist in redistributing stresses placed on theimplant body 10. - The
implant body 10 is preferably used in conjunction with ananti-rotational plug 56 such as illustrated in FIGS. 9-12. Theplug 56 acts as a host for all coronal attachments. Theplug 56 has adistal moiety 58, acoronal moiety 60, and alongitudinal axis 62. Thedistal moiety 58 is sized and dimensioned to match the coronal bore 44 of theimplant body 10 so that theplug 56 can be firmly affixed therein. Theplug 56 may also be designed with parallel walls as shown in FIG. 9A to assure parallelism between thelongitudinal axis 26 of theimplant body 10 and the longitudinal axis of theplug 56 during assembly. In this case, a Mores taper would preferably be defined in the attachment structure (described below). Thecoronal moiety 60 of theplug 56 would be machined most preferably at a 2° Mores taper to assure accuracy and stability. - The
coronal moiety 60 has a maximum cross-section perpendicular to thelongitudinal axis 62 of theplug 56 which is smaller than the maximum cross-section of thedistal moiety 58 perpendicular to thelongitudinal axis 62 of theplug 56. As can be seen from FIG. 13 (which illustrates atypical plug 56 disposed within an implant 10), the fact that thecorona moiety 60 of theplug 56 has a smaller cross-section than thedistal moiety 58, results in anannular gap 64 between theinner surface 66 of the coronal bore 44 within theimplant body 10 and thecoronal moiety 60 of theplug 56. As will be shown below, thisannular gap 64 facilitates the "countersinking" of the prosthesis attachment structure (described below) to the implant body-plug combination 67. Alternatively, the tapered segment which creates theannular gap 64 may be defined in the prosthesis attachment structure in both theplug 56 and the prosthesis attachment structure to create an intimate fit upon proper seating. - The
coronal moiety 60 of theplug 56 has at least one cross-section perpendicular to thelongitudinal axis 62 of the plug which is non-circular. As will be seen below, this important feature allows for the reinstallation of an attachment structure (which has been previously removed from thecoronal moiety 60 of the plug 56) to precisely the original location. The non-circular cross-section of thecoronal moiety 60 can take on any of a wide variety of shapes. As shown in FIG. 10, thecoronal moiety 60 of theplug 56 has a single cam projection 68. In the embodiment illustrated in FIG. 12, thecoronal moiety 60 of theplug 56 has a hexagonal cross-section. Key-ways, locking splines, slots, flats and other cross-sectional shapes can also be used. - The
coronal moiety 60 has an internally threaded plug bore 70 disposed along thelongitudinal axis 62 of theplug 56. This threaded plug bore 70 facilitates the installation of aprosthesis 12 or other attachments to theplug 56 by providing an attachment site for an attachment screw. - Regardless of the shape of the
coronal moiety 60 of theplug 56, it is preferred that thecoronal moiety 60 be slightly tapered. It is most preferred that such tapering be a Mores taper 71 of between about 1° and about 2°, ideally, 1°, 30'. Such taper facilitates the installation of an attachment structure to thecoronal moiety 60. - In practice, the
plug 56 is disposed within theimplant body 10 as illustrated in FIGS. 13-14. Theplug 56 can be welded within theimplant body 10, cemented, or attached by any other suitable means. - The
distal end 58 of theplug 56 is slightly typically tapered as is thedistal section 46 of the coronal bore 44 within theimplant body 10. Such matched tapering facilitates the installation of theplug 56 within theimplant body 10. Alternatively, theplug 56 is not tapered. This shape may be preferred to assure proper orientation of theplug 56 prior to welding within theimplant body 10. - FIGS. 15-17 illustrate a
typical healing cap 72 useful in the invention. Thehealing cap 72 can be used to seal the coronal end 74 of the tapered implant body-plug combination 67 after the combination 67 has been implanted into a patient (as illustrated in FIGS. 18 and 19). Thehealing cap 72 has acap portion 78 sized and dimensioned to match up with thecoronal end 18 of theimplant body 10. Thehealing cap 72 also has a threadeddistal end 80 sized and dimensioned to thread into the internally threaded plug bore 70 of theplug 56. Thecap portion 78 has acoronal bore 82 with a non-circular cross-section. This bore 82 is adapted to accept a torquing tool which can be used to thread thehealing cap 72 into thecoronal moiety 60 of theplug 56. - FIGS. 20-21 illustrate a
typical attachment structure 84 useful for attaching impression attachments, prostheses or other attachments to the implant body-plug combination 67. Theattachment structure 84 comprises an elongatedhollow section 86 having acoronal moiety 88 with an opencoronal end 90, adistal moiety 92 with an opendistal end 94 and alongitudinal axis 96. Thedistal end 92 of theattachment structure 84 is shaped and dimensioned to receive and engage the non-circular cross-section of thecoronal moiety 60 of theplug 56. In the embodiment shown in the drawings, thedistal end 94 of theattachment structure 84 is shaped to receive thecoronal end 60 of aplug 56 having a cam projection 68, such as illustrated in FIG. 9. As mentioned above, this feature allows the practitioner to remove theattachment structure 84 from theplug 56 and thereafter reinstall theattachment structure 84 onto theplug 56 in precisely the same alignment in which it was initially installed. Alternatively, one or both components may also be machined parallel and alone be tapered to achieve the same results. Thecoronal moiety 88 is preferably detachable from thedistal moiety 92. - The
attachment structure 84 can be affixed to theplug 56 by an elongatedfirst screw 98 which is disposed within thehollow section 86 of theattachment structure 84. Such afirst screw 98 is illustrated in FIGS. 22 and 23. The threads of thefirst screw 98 are chosen to match the internal threads in thebore 70 of theplug 56. FIG. 24 illustrates thefirst screw 98 disposed within theattachment structure 84. Thefirst screw 98 has acoronal bore 99 with a non-circular cross-section. This bore 99 is adapted to accept a torquing tool which can be used to thread thefirst screw 98 into thecoronal moiety 60 of theplug 56. - In the embodiments illustrated in the drawings, the
distal moiety 92 of theattachment structure 84 has a firstexternal surface section 100 immediately proximate to thedistal end 94 of theattachment structure 84 and a secondexternal surface section 102 immediately proximate to the firstexternal surface section 100. The cross-sections of the first and secondexternal surface sections implant body 10 immediately proximate to thecoronal end 18 of theimplant body 10. Thewidth 103 of the firstexternal surface section 100 is substantially the same as the depth 104 of thecoronal section 48 of the implant body coronal bore 44. As shown in FIG. 25, this design allows the firstexternal surface section 100 to nest within thecoronal section 48 of the coronal bore 44 of theimplant body 10. The diameter of the secondexternal surface section 102 is substantially the same as the diameter of the external surface of theimplant body 10 immediately proximate to itscoronal end 18. As illustrated in FIG. 25, this provides for a smooth transitional surface between theimpact body 10 and theattachment structure 84. - FIGS. 25-27 illustrate the
attachment structure 84 as it is combined with theimplant body 10 and theplug 56, using thefirst screw 98. - FIG. 28 illustrates the combination illustrated in FIG. 25 in further combination with a
dental prosthesis 12 attached to theattachment structure 84. - In many cases prior to the final installation of the
prosthesis 12 onto theattachment structure 84, it is desirable to cover theattachment structure 84 with asheath 106. Such asheath 106 is illustrated in FIGS. 31-33. As shown in FIG. 31, to install thesheath 106, the practitioner first removes thecoronal moiety 88 of theattachment structure 84. Thesheath 106 can be made of a plastic material. Other suitable materials can, of course, be used, i.e., Ti, Ti 6-4 alloy or Ti 13-13, etc. - The
sheath 106 has an opencoronal end 108 and an opendistal end 110. Thecoronal end 108 is sized and dimensioned to cover thecoronal end 90 of theattachment structure 84. Theopening 112 in thecorona end 108 of thesheath 106 is sized and dimensioned to receive asecond screw 114 as illustrated in FIGS. 34 and 35. Thesecond screw 114 is threaded in such a way that it can be attached within thebore 70 of theplug 56. Thesecond screw 114 has ashoulder 116 sized and dimensioned to firmly retain theattachment structure 84 to theplug 56. Thesecond screw 114 also has ahead 118 sized and dimensioned to firmly attach thesheath 106 to theattachment structure 84. Thesecond screw 114 has acoronal bore 119 with a non-circular cross-section. This bore 119 is adapted to accept a torquing tool which can be used to thread thesecond screw 114 into thecoronal moiety 60 of theplug 56. - As illustrated in FIG. 36, the implant body-
plug combination 76 can be conveniently packaged with animplant tool 120 within aprotective cover 122 so that the practitioner can quickly and easily install the implant body-plug combination 76 by merely removing thecover 122 and using theinstallation tool 120 to install theimplant body 10 within a pre-prepared implant site. Atypical implant tool 120 is illustrated in FIGS. 37-44. - The
tool 120 comprises ashank portion 124 which is attachable to aremovable handle portion 126. Thedistal end 128 of theshank portion 124 is sized and dimensioned to match up and engage thecoronal moiety 60 of theplug 56 and thecoronal end 18 of theimplant body 10. Thedistal end 128 of theshank 124 is sized and dimensioned to accept theremovable handle portion 126. Both thehandle portion 126 and theshank 124 are hollow so that athird screw 130 can be used to firmly attach thehandle portion 126 to theshank 124 and theshank 124 to theplug 56 as illustrated in FIG. 36. Thethird screw 130 has acoronal bore 131 with a non-circular cross-section. This bore 131 is adapted to accept a torquing tool which can be used to thread thethird screw 130 into thecoronal moiety 60 of theplug 56. - In practice, the implant body of the
invention 10 is installed into an implant site which has been previously prepared in thebone 3 of the patient. Such an implant site can be prepared using tapered drills such as those illustrated in FIGS. 45-50. The drill illustrated in FIG. 45 is atypical pilot drill 132. The drill illustrated in FIG. 48 is alarger drill 134 for use after a pilot hole is drilled (by thepilot 132 drill) to prepare the full dimension of the implant site. - Although the present invention has been described in considerable detail with reference to certain preferred versions, many other versions should be apparent to those skilled in the art. Therefore, the spirit and scope of the appending claims should not necessarily be limited to the description of the preferred versions contained herein.
Claims (22)
- An endosseous implant body for implantation into bone, the body having a coronal end, a distal end, a longitudinal axis and a plurality of segments proximate to the coronal end, wherein:(a) each segment has a circular cross-section perpendicular to the longitudinal axis and comprises a frustro-conical compression moiety and a frustro-conical tension moiety, both moieties have a maximum diameter, a minimum diameter and a substantially flat surface area disposed therebetween at an angle of incidence with respect to the longitudinal axis, the maximum diameter of the compression moiety being the same as the maximum diameter of the tension moiety and the compression moiety being joined to the tension moiety along each moiety's respective maximum diameter;(b) the minimum diameter of each compression moiety is identical to and is attached to the minimum diameter of a tension moiety of an adjacent segment;(c) the angles of incidence and the surface areas of the compression moieties are chosen so that, when the implant body is implanted into bone and a lateral force is applied to the coronal end of the implant body, that portion of the lateral force which is exerted by the compression moiety of each segment against the surrounding bone is greater than that portion of the lateral force which is exerted by the compression moiety of an adjacent segment disposed more proximate to the coronal end; and(d) the angles of incidence and the surface areas of the tension moieties are chosen so that when the implant body is implanted into bone and a lateral force is applied to the coronal end of the implant body, that portion of the lateral force which is exerted by the tension moiety of each segment against the surrounding bone is less than that portion of the lateral force which is exerted by the tension moiety of an adjacent segment disposed more proximate to the coronal end.
- The implant body of Claim 1 having at least four segments and wherein the distance between the minimum diameter of the compression segment nearest the coronal end and the minimum diameter of the tension moiety most distal from the coronal end is between about 4 and about 8 millimeters.
- The implant body of Claim 1 wherein the distance between the coronal end and the distal end is between about 8 and about 18 millimeters.
- The implant body of Claim 1 wherein the width of each compression moiety surface between the minimum diameter of the compression' moiety and the maximum diameter of the compression moiety is greater than the width of the compression moiety surface between the minimum diameter of the compression moiety and the maximum diameter of the compression moiety of an adjacent segment disposed more proximate to the distal end.
- The implant body of Claim 1 wherein the width of each tension moiety surface between the minimum diameter of the tension moiety and the maximum diameter of the tension moiety is greater than the width of the tension moiety surface between the minimum diameter of the tension moiety and the maximum diameter of the tension moiety of an adjacent segment disposed more proximate to the coronal end.
- The implant body of Claim 1 wherein the angle of incidence of each compression moiety surface between the minimum diameter of the compression moiety and the maximum diameter of the compression moiety is greater than the angle of incidence of the compression moiety surface between the minimum diameter of the compression moiety and the maximum diameter of the compression moiety of an adjacent segment disposed more proximate to the distal end.
- The implant body of Claim 1 wherein the angle of incidence of each tension moiety surface between the minimum diameter of the tension moiety and the maximum diameter of the tension moiety is greater than the angle of incidence of the tension moiety surface between the minimum diameter of the tension moiety and the maximum diameter of the tension moiety of the tension moiety of an adjacent segment disposed more proximate to the coronal end.
- The implant body of Claim 1 wherein the coronal end defines a tapered coronal bore having circular cross-sections perpendicular to the longitudinal axis, and wherein the coronal bore comprises a tapered distal section and a coronal section, the coronal section having a substantially circular cross-section which is greater than the maximum cross-section of the distal section.
- The implant body of Claim 1 wherein the exterior surface proximate to the distal end is externally threaded.
- The implant body of Claim 1 wherein the exterior surface proximate to the distal end is externally knurled.
- An endosseous implant combination comprising:(a) an implant body having a distal end, a coronal end and a longitudinal axis, the coronal end defining a tapered coronal bore having circular cross-sections perpendicular to the longitudinal axis; and(b) a plug having a distal moiety, a coronal moiety and a longitudinal axis, the distal moiety being sized and dimensioned to match the coronal bore of the implant body and being affixed therein, the coronal moiety having a maximum cross-section perpendicular to the longitudinal axis which is smaller than the maximum cross-section of the distal moiety perpendicular to the longitudinal axis, the coronal moiety having at least one cross-section perpendicular to the longitudinal axis which is non-circular and the coronal moiety defining an internally threaded plug bore disposed along the longitudinal axis of the plug.
- The combination of Claim 11 wherein the coronal moiety of the plug is tapered to a Mores taper of between about one degree and about two degrees.
- The combination of Claim 11, wherein the distal moiety of the plug is tapered.
- The combination of Claim 11, wherein the distal moiety of the plug is not tapered.
- The combination of Claim 12 wherein the coronal moiety of the plug has at least one cross-section which is substantially hexagonal.
- The combination of Claim 11 wherein the implant body coronal bore has a distal section and a coronal section, the distal section being tapered and having a maximum cross-sectional diameter which is less than the cross-sectional diameter of the corona section and wherein the plug is disposed within the distal section of the implant body coronal bore.
- The combination of Claim 11 further comprising an attachment structure, the attachment structure comprising an elongated hollow section having a coronal moiety with an open coronal end, a distal moiety with an open distal end and a longitudinal axis, the distal end of the attachment structure being shaped and dimensioned to receive and engage the non-circular cross-section of the coronal moiety of the plug, the attachment structure being affixed to the plug by an elongated screw disposed within the hollow section, the screw having a head and an externally threaded end, the threaded end being threaded into the plug bore, whereby the head of the screw is accessed for applying torque to the screw through the open proximal end of the attachment structure.
- The combination of Claim 17 wherein:(a) the implant body coronal bore has a distal section and a coronal section, the distal section being tapered and having a maximum cross-sectional diameter which is less than the cross-sectional diameter of the coronal section;(b) the distal moiety of the attachment structure has a first external surface section immediately proximate to the distal end of the attachment structure and a second external surface section immediately proximate to the first external surface section;(c) the cross-sections of the first and second external surface sections are substantially circular as is the cross-section of the external surface of the implant body immediately proximate to the coronal end;(d) the diameter of the first external surface section is substantially the same as the cross-sectional diameter of the coronal section of the implant body coronal bore and the diameter of the second external surface section is substantially the same as the external diameter of the external surface of the implant body immediately proximate to the coronal end; and(e) the width of the first external surface section is substantially the same as the depth of the coronal section of the implant body coronal bore.
- The combination of Claim 17 further comprising a sheath for securely covering the open proximal end of the attachment structure, the sheath having a hollow body with an open distal end and an open proximal end, the open distal end being sized and dimensioned to conform to the proximal end of the attachment structure so that the sheath securely engages the proximal end of the attachment structure, the sheath being attached to the attachment structure by a screw engaged into the distal bore of the plug, the screw having a head and an externally threaded end, the threaded end being threaded into the plug bore and the head of the screw being accessed for applying torque to the screw through the open proximal end of the attachment structure.
- The combination of Claim 17 further comprising a dental prosthesis attached to the proximal end of the attachment structure.
- The combination of Claim 11 further comprising a healing cap having a threaded distal end and a coronal head, the threaded distal end being adapted to thread within the plug bore and the coronal head being sized and dimensioned to cover the coronal end of the implant body, the healing cap further comprising a coronal bore disposed coaxially with the longitudinal axis of the implant body and having a non-circular interior cross-section.
- An endosseous implant delivery system combination comprising:(a) an implant body having a distal end, a coronal end and a longitudinal axis, the coronal end defining a tapered coronal bore having circular cross-sections perpendicular to the longitudinal axis;(b) a plug having a distal moiety, a coronal moiety and a longitudinal axis, the distal moiety being sized and dimensioned to match the coronal bore of the implant body and being affixed therein, the coronal moiety having a maximum cross-section perpendicular to the longitudinal axis which is smaller than the maximum cross-section of the distal moiety perpendicular to the longitudinal axis, the coronal moiety having at least one cross-section perpendicular to the longitudinal axis which is non-circular and the coronal moiety defining a threaded plug bore disposed along the longitudinal axis of the plug; and(c) an elongated hollow wrench having a hollow body, an open proximal end and an open distal end, the distal end being shaped and dimensioned to receive and engage the non-circular cross-section of the coronal moiety of the plug, the wrench being attached to the plug by an elongated screw disposed within the hollow body of the wrench, the screw having a head and an externally threaded end, the threaded end being threaded into the plug bore, whereby the head of the screw is accessed for applying torque to the screw through the open proximal end of the wrench.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/288,278 US5527183A (en) | 1993-08-18 | 1994-08-09 | Endosseous implant system |
US288278 | 1999-04-08 |
Publications (1)
Publication Number | Publication Date |
---|---|
EP0696445A1 true EP0696445A1 (en) | 1996-02-14 |
Family
ID=23106464
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP95302105A Ceased EP0696445A1 (en) | 1994-08-09 | 1995-03-29 | Endosseous implant system |
Country Status (2)
Country | Link |
---|---|
US (1) | US5527183A (en) |
EP (1) | EP0696445A1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2005030081A1 (en) * | 2003-10-01 | 2005-04-07 | Nobel Biocare Ab (Publ) | Implant arrangement with an internal socket for a turning tool |
WO2010006740A3 (en) * | 2008-07-14 | 2010-08-26 | Nobel Biocare Services Ag | Compact dental implant |
Families Citing this family (70)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5816812A (en) * | 1994-07-22 | 1998-10-06 | Osteomed Corporation | Dental implant fixture |
US5749732A (en) * | 1995-10-03 | 1998-05-12 | Sendax; Victor | Dental implantation |
US5904483A (en) * | 1995-11-17 | 1999-05-18 | Wade; Curtis K. | Dental implant systems and methods |
ES2134646T3 (en) * | 1995-12-04 | 1999-10-01 | Straumann Inst Ag | HEALING HOOD FOR A DENTAL IMPLANT. |
DE69738492T2 (en) * | 1996-09-30 | 2009-01-15 | Brainbase Corp. | Implant with bioactive particles and process for its preparation |
US5795160A (en) * | 1997-02-06 | 1998-08-18 | Hahn; Jack A. | Tapered dental implant in a stepped orifice |
US5899940A (en) * | 1997-02-11 | 1999-05-04 | Carchidi; Joseph Edward | Maxillofacial anchoring system for alveolar and small bone skeletal distraction |
US5954504A (en) * | 1997-03-31 | 1999-09-21 | Biohorizons Implants Systems | Design process for skeletal implants to optimize cellular response |
US20080032263A1 (en) * | 2006-08-01 | 2008-02-07 | Vitali Bondar | Dental Implant System and Method |
US5842865A (en) * | 1997-09-12 | 1998-12-01 | Sulzer Calcitek Inc. | Self-tapping implant with multiple concave tapping channels |
US5897319A (en) * | 1997-09-12 | 1999-04-27 | Sulzer Calcitek Inc. | Self-tapping implant with helical flutes |
SE516917C2 (en) | 1997-11-11 | 2002-03-19 | Nobel Biocare Ab | Device for providing reliable anchoring of threaded implants in bone |
SE9802572D0 (en) | 1998-07-17 | 1998-07-17 | Astra Ab | Dental implant |
SE9802571D0 (en) * | 1998-07-17 | 1998-07-17 | Astra Ab | Implant |
SE9802603D0 (en) * | 1998-07-23 | 1998-07-23 | Astra Ab | Dental implant component |
SE9802605D0 (en) | 1998-07-23 | 1998-07-23 | Astra Ab | Dental implant component |
US5967783A (en) * | 1998-10-19 | 1999-10-19 | Ura; Robert S. | Threaded dental implant with a core to thread ratio facilitating immediate loading and method of installation |
US8043089B2 (en) | 1999-04-23 | 2011-10-25 | 3M Innovative Properties Company | One piece dental implant and use thereof in prostodontic and orthodontic applications |
US6280191B1 (en) | 1999-09-03 | 2001-08-28 | Christopher B. Gordon | Distractor suitable for permanent implantation into bone |
IT1314729B1 (en) * | 2000-05-10 | 2003-01-03 | Physioplant S R L | PROSTHETIC DEVICE FOR INTRA-BONE DENTAL IMPLANTS |
US6402515B1 (en) | 2001-01-10 | 2002-06-11 | Sulzer Dental Inc. | Dental implant with variable profile thread |
DE10114627A1 (en) * | 2001-03-23 | 2002-10-02 | Herbert Hatzlhoffer | implant |
SE0102749D0 (en) * | 2001-08-15 | 2001-08-15 | Astra Tech Ab | Implant, arrangement including an implant, and method of inserting said implant into bone tissue |
GB0123804D0 (en) * | 2001-10-04 | 2001-11-21 | Osseobiotek Ltd | Implant |
AU2002357086A1 (en) * | 2001-12-07 | 2003-06-23 | Nobel Biocare Ab | Healing abutment |
SE520756C2 (en) * | 2001-12-21 | 2003-08-19 | Nobel Biocare Ab | Method of providing surface structure on implants as well as such implants |
SE523395C2 (en) | 2001-12-21 | 2004-04-13 | Nobel Biocare Ab | Implants and methods and systems for providing such implants |
JP2003222116A (en) * | 2002-01-31 | 2003-08-08 | Honda Motor Co Ltd | Self-tapping bolt |
DE10216713B4 (en) * | 2002-04-10 | 2006-01-05 | Eska Implants Gmbh & Co. | Set for creating a dental total replacement implant |
US7005974B2 (en) * | 2002-04-19 | 2006-02-28 | Donnelly Corporation | Vehicle imaging system |
US20060063133A1 (en) * | 2002-09-30 | 2006-03-23 | Robert Schroering | Dental implant |
SE526667C2 (en) * | 2002-12-30 | 2005-10-25 | Nobel Biocare Ab | Device for implants and method for making the implant |
US20040241610A1 (en) * | 2003-01-03 | 2004-12-02 | Steve Hurson | Dental implant system |
US8651863B2 (en) * | 2003-04-01 | 2014-02-18 | Robert Schroering | Band of connective tissue grooves for use with a dental implant or a separate abutment for a dental implant |
IL156033A0 (en) | 2003-05-21 | 2004-03-28 | Ophir Fromovich Ophir Fromovic | Dental implant |
US7014464B2 (en) * | 2003-12-19 | 2006-03-21 | Niznick Gerald A | Multi-part abutment and transfer cap for use with an endosseous dental implant with non-circular, beveled implant/abutment interface |
GB2416012B (en) * | 2004-07-09 | 2007-05-09 | Bae Systems Plc | Fastener arrangement for fastening a detachable panel |
US20060263747A1 (en) * | 2005-03-17 | 2006-11-23 | Hurson Steven M | Healing cap for dental implants |
EP1885277A1 (en) * | 2005-03-17 | 2008-02-13 | Nobel Biocare Services AG | Transfer coping for dental implants |
DE202006006920U1 (en) * | 2006-04-25 | 2007-08-30 | Biomed Est. | Orthopedic anchoring system, for fixation of long bone e.g. tibia, fracture, has two lateral implants, where each implant includes base and post that are arranged orthogonally and coated with active substances |
US8100946B2 (en) | 2005-11-21 | 2012-01-24 | Synthes Usa, Llc | Polyaxial bone anchors with increased angulation |
US8740947B2 (en) * | 2006-02-15 | 2014-06-03 | Warsaw, Orthopedic, Inc. | Multiple lead bone fixation apparatus |
WO2008016917A2 (en) * | 2006-08-01 | 2008-02-07 | Vitali Bondar | Dental implant system and method |
WO2008121928A2 (en) * | 2007-03-31 | 2008-10-09 | 3M Imtec Corporation | Implant thread design |
US8038442B2 (en) | 2007-04-23 | 2011-10-18 | Nobel Biocare Services Ag | Dental implant and dental component connection |
US7806693B2 (en) * | 2007-04-23 | 2010-10-05 | Nobel Biocare Services Ag | Dental implant |
WO2009009897A1 (en) * | 2007-07-16 | 2009-01-22 | Laszlo Kalman | A dental prosthesis abutment system and method for using same |
PL2170192T3 (en) * | 2007-07-20 | 2011-07-29 | Synthes Gmbh | Polyaxial bone fixation element |
US9439681B2 (en) | 2007-07-20 | 2016-09-13 | DePuy Synthes Products, Inc. | Polyaxial bone fixation element |
FR2930134B1 (en) * | 2008-04-16 | 2011-05-20 | Pierre Malek | PROGRESSIVE THREADING RADIAL PIVOT OF VARIABLE DEPTH FOR ITS DISASSEMBLY |
US20090298015A1 (en) * | 2008-05-28 | 2009-12-03 | Global Implant Solutions, Llc | Digital Abutment For Dental Implant System |
US20100015571A1 (en) * | 2008-07-15 | 2010-01-21 | Global Implant Solutions, Llc | Flexible Abutment For Use With A Dental Implant |
WO2010028287A2 (en) | 2008-09-05 | 2010-03-11 | Synthes Usa, Llc | Bone fixation assembly |
JP5815407B2 (en) | 2008-09-12 | 2015-11-17 | ジンテス ゲゼルシャフト ミット ベシュレンクテル ハフツング | Spinal stabilization and guided fixation system |
WO2010037098A1 (en) | 2008-09-29 | 2010-04-01 | Synthes Usa, Llc | Polyaxial bottom-loading screw and rod assembly |
EP2376005B1 (en) | 2008-11-03 | 2016-05-18 | Synthes GmbH | Uni-planar bone fixation assembly |
CN102368967B (en) | 2009-04-15 | 2016-03-02 | 斯恩蒂斯有限公司 | For the revision connector of spinal structure |
WO2010148231A1 (en) | 2009-06-17 | 2010-12-23 | Synthes Usa, Llc | Revision connector for spinal constructs |
US9693837B2 (en) | 2009-08-06 | 2017-07-04 | Sue S. Lee | Dental implant |
US9763717B2 (en) | 2010-03-03 | 2017-09-19 | Luis Mauricio Chiquillo Perez | Multi-tapered implant screw |
EP2618774B1 (en) | 2010-09-23 | 2017-11-15 | Biomet 3i, LLC | Dental abutment system |
EP2468210B1 (en) * | 2010-12-23 | 2015-11-11 | Straumann Holding AG | Improved screw head |
CN103445874A (en) * | 2012-05-31 | 2013-12-18 | 医桥科技股份有限公司 | Artificial tooth root |
CL2015001657S1 (en) | 2014-12-15 | 2016-09-02 | Jjgc Indústria E Comércio De Materiais Dentários S A | Configuration applied to bone implant. |
BR102014031426B1 (en) | 2014-12-15 | 2018-07-24 | Jjgc Ind E Comercio De Materiais Dentarios S/A | implant |
US10413387B2 (en) | 2015-01-20 | 2019-09-17 | John Andler | Threaded dental implant |
US10743966B2 (en) * | 2015-01-21 | 2020-08-18 | Kwang Seob Kim | Implant unit |
US10980617B2 (en) * | 2015-02-23 | 2021-04-20 | Maurice Valen | Implantable surgical screw for bone reconstruction |
BR102016010184B1 (en) | 2016-05-05 | 2020-10-27 | Jjgc Indústria E Comércio De Materiais Dentários S.A. | prosthetic set and process for producing the same |
US11559375B2 (en) * | 2020-07-16 | 2023-01-24 | Leszek Aleksander Tomasik | Diamond dental teeth formed by using laser energy |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4270905A (en) * | 1979-02-21 | 1981-06-02 | Mohammed M Hamdi A | Replacement system for dental and other bone implants |
US4437191A (en) * | 1981-04-03 | 1984-03-20 | Delphi Dental Industries B.V. | Implant of ceramic material |
US4792339A (en) * | 1985-05-23 | 1988-12-20 | Laboratorium Fur Experiementelle Chirurgie, Forschungsinstitut | Self-locking stemmed component for a joint endo-prosthesis |
DE3811498A1 (en) * | 1988-04-06 | 1989-10-26 | Witzel Ulrich | Dental jaw implant |
US5222983A (en) * | 1990-09-13 | 1993-06-29 | Thera Patent Gmbh & Co. | Implantable prosthesis |
Family Cites Families (95)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US711324A (en) * | 1902-02-15 | 1902-10-14 | William Peter Lacy | Artificial denture. |
US866304A (en) * | 1904-04-18 | 1907-09-17 | Finis E Roach | Removable artificial denture. |
DE604674C (en) * | 1931-01-01 | 1934-10-29 | Wesley Ernest John | Process for the production of lens mounts |
US2112007A (en) * | 1937-01-16 | 1938-03-22 | Pinkney B Adams | Anchoring means for false teeth |
US2347567A (en) * | 1943-03-11 | 1944-04-25 | Edward J Kresse | Dental implant |
US2609604A (en) * | 1949-02-14 | 1952-09-09 | Boyd F Sprague | Dental screw insert |
GB660342A (en) * | 1949-11-07 | 1951-11-07 | Edmund Nuttall Sons & Company | Improvements in and relating to anchorage means for use in concrete and like constructions |
BE517055A (en) * | 1952-01-21 | |||
US2774141A (en) * | 1953-03-23 | 1956-12-18 | William T Quinn | Pontics for dental bridges |
GB968672A (en) * | 1959-10-16 | 1964-09-02 | Baker & Finnemore Ltd | Improvements in and relating to screws with false heads for disguising their ends |
GB937944A (en) * | 1961-08-05 | 1963-09-25 | Erich Hensel | Improvements in or relating to bolt devices |
US3499222A (en) * | 1965-08-17 | 1970-03-10 | Leonard I Linkow | Intra-osseous pins and posts and their use and techniques thereof |
US3435526A (en) * | 1967-02-13 | 1969-04-01 | Heli Coil Corp | Device for securing an artificial tooth to the bone structure of a human jaw |
GB1203093A (en) * | 1967-09-15 | 1970-08-26 | Alfred Edward Edelman | Implant prostheses for dentistry. |
SE332486B (en) * | 1968-12-09 | 1971-02-08 | Aga Ab | |
SE328961B (en) * | 1970-03-25 | 1970-09-28 | Aga Ab | |
US3849887A (en) * | 1970-06-01 | 1974-11-26 | Vitredent Corp | Dental implant |
US3729825A (en) * | 1971-08-02 | 1973-05-01 | Oratronics Inc | Oral implant |
US3787975A (en) * | 1972-09-18 | 1974-01-29 | M Zuest | Anchor for attaching dental partial or full artificial denture |
US3919774A (en) * | 1973-08-28 | 1975-11-18 | Mark J Fishman | Combination endodontic apical sealer and crown post |
US3849888A (en) * | 1973-10-19 | 1974-11-26 | Oratronics Inc | Bone adapting tissue packing post system |
JPS5223514B2 (en) * | 1974-09-25 | 1977-06-24 | ||
US4187609A (en) * | 1975-03-17 | 1980-02-12 | Edelman Alfred E | Submerged functional implant and method |
DE2611744C2 (en) * | 1976-03-19 | 1982-01-28 | Werner Dipl.-Ing. 8000 Muenchen Kraus | Device for maintaining the vitality of bone tissue for endoprostheses |
US4053982A (en) * | 1976-03-23 | 1977-10-18 | Bernard Weissman | Dental anchor |
DE2619650C3 (en) * | 1976-05-04 | 1985-06-05 | Friedrichsfeld Gmbh, Steinzeug- Und Kunststoffwerke, 6800 Mannheim | Dental implant |
US4109383A (en) * | 1976-06-21 | 1978-08-29 | Reed Gerald M | Dental implant bender |
GB1565178A (en) * | 1977-02-24 | 1980-04-16 | Interfix Ltd | Bone screw |
US4259072A (en) * | 1977-04-04 | 1981-03-31 | Kyoto Ceramic Co., Ltd. | Ceramic endosseous implant |
US4177562A (en) * | 1977-05-02 | 1979-12-11 | Miller Alvin L | Dental implant and method of inserting the same |
CH618870A5 (en) * | 1977-10-31 | 1980-08-29 | Straumann Inst Ag | |
US4204321A (en) * | 1978-03-24 | 1980-05-27 | Scott Edward S | Dental post |
US4290755A (en) * | 1979-03-05 | 1981-09-22 | Scott Edward S | Dental post and method of installing |
CH634220A5 (en) * | 1979-11-05 | 1983-01-31 | Borle Jean Pierre | ANCHOR SCREW FOR DENTAL FILLING AND TOOL FOR FORMING A HOLLOW TO PLACE THIS SCREW. |
CH642838A5 (en) * | 1979-11-21 | 1984-05-15 | Osteo Ag | JAW IMPLANT. |
US4302188A (en) * | 1980-01-24 | 1981-11-24 | Bio-Dynamics, Inc. | Prosthetic dental implants |
CH648197A5 (en) * | 1980-05-28 | 1985-03-15 | Synthes Ag | IMPLANT AND SCREW FASTENING ON ITS BONE. |
CH651747A5 (en) * | 1981-08-20 | 1985-10-15 | Straumann Inst Ag | IMPLANT FOR FASTENING AN ARTIFICIAL DENTAL REPLACEMENT. |
SE453356B (en) * | 1981-11-16 | 1988-02-01 | Barry L Musikant | SCREW PIN FOR INSERTING IN A DENTAL ROUTE |
US4359318A (en) * | 1981-12-18 | 1982-11-16 | Neal Gittleman | Dental implant |
GB2117641B (en) * | 1982-03-24 | 1985-03-27 | Winter Moore Peter Howard | Dental post assembly |
US4431416A (en) * | 1982-04-29 | 1984-02-14 | A & L Investment Company | Endosseous dental implant system for overdenture retention, crown and bridge support |
US4488875A (en) * | 1982-04-29 | 1984-12-18 | A&L Investment Company | Connector for overdenture |
US4416629A (en) * | 1982-07-06 | 1983-11-22 | Mozsary Peter G | Osseointerfaced implanted artificial tooth |
DE3241963C1 (en) * | 1982-11-12 | 1984-04-26 | Feldmühle AG, 4000 Düsseldorf | Helical jaw implant |
US4573922A (en) * | 1983-01-31 | 1986-03-04 | Bello Lino L | Artificial endo-osseous pillar for supporting fixed prosthetic members |
US4552532A (en) * | 1983-12-12 | 1985-11-12 | Mozsary Peter G | Osteocorrective dentoalveolar implant system |
DE3423752A1 (en) * | 1984-04-14 | 1985-10-24 | Hans 2800 Bremen Grafelmann | Intraossal leaf implant |
DE3421056A1 (en) * | 1984-06-06 | 1985-12-12 | Feldmühle AG, 4000 Düsseldorf | JAW IMPLANT FOR THE ADMISSION OF A DENTAL SPARE CARRIER |
US4645453A (en) * | 1985-09-19 | 1987-02-24 | Niznick Gerald A | Bendable adapter for dental implant |
US4661066A (en) * | 1985-11-25 | 1987-04-28 | Linkow Leonard I | Movable plate implant |
US4842518A (en) * | 1986-09-04 | 1989-06-27 | Vent-Plant Corporation | Submergible screw-type dental implant and method of utilization |
US4713004A (en) * | 1986-09-04 | 1987-12-15 | Vent Plant Corporation | Submergible screw-type dental implant and method of utilization |
US4932868A (en) * | 1986-09-04 | 1990-06-12 | Vent-Plant Corporation | Submergible screw-type dental implant and method of utilization |
US4780080A (en) * | 1987-01-05 | 1988-10-25 | Facial Alveodental Implant Rehabilitation Inc. | Adjustable dentoalveolar implant system |
US5061181A (en) * | 1987-01-08 | 1991-10-29 | Core-Vent Corporation | Dental implant including plural anchoring means |
US5078607A (en) * | 1987-01-08 | 1992-01-07 | Core-Vent Corporation | Dental implant including plural anchoring means |
CA1322481C (en) * | 1987-01-08 | 1993-09-28 | Gerald A. Niznick | Dental implant anchor carrying plural anchoring means |
GB2199626B (en) * | 1987-01-08 | 1991-09-04 | Core Vent Corp | Screw-type dental implant anchor |
SE456216B (en) * | 1987-04-22 | 1988-09-19 | Astra Meditec Ab | TOOLS FOR A PROTEST PART |
US4944754A (en) * | 1987-04-29 | 1990-07-31 | Vent-Plant Corporation | Method of manufacturing synthetic bone coated surgical implants |
US4908030A (en) * | 1987-04-29 | 1990-03-13 | Vent-Plant Corporation, Inc. | Method of manufacturing synthetic bone coated surgical implants |
US4856994A (en) * | 1988-01-25 | 1989-08-15 | Implant Innovations, Inc. | Periodontal restoration components |
US4904187A (en) * | 1988-04-13 | 1990-02-27 | Tri-Stage, Inc. | Dental implant |
BE1002350A3 (en) * | 1988-08-02 | 1991-01-08 | Dury Georges Emile Ladislas | IMPLANT. |
FR2635964A1 (en) * | 1988-09-02 | 1990-03-09 | Poulmaire Francis | System which can be implanted with or without resilience, rotary device for producing the implant housing and method for using the implantable system |
US5180303A (en) * | 1988-09-21 | 1993-01-19 | Regents Of The University Of California | Retrievable dental prothesis apparatus and method of fabrication |
US5076788A (en) * | 1988-10-05 | 1991-12-31 | Core-Vent Corporation | Grooved, cylindrical dental implant anchoring means |
US4915628A (en) * | 1988-12-14 | 1990-04-10 | Vent-Plant Corporation, Inc. | Submergible dental implant and method of utilization |
US5030095A (en) * | 1989-08-16 | 1991-07-09 | Niznick Gerald A | Angled abutment for endosseous implants |
WO1991003213A1 (en) * | 1989-08-30 | 1991-03-21 | Tdk Corporation | Artificial dental root |
US5254005A (en) * | 1989-11-14 | 1993-10-19 | Max Zuest | Dental implant system and method |
FR2655534B1 (en) * | 1989-12-12 | 1997-10-24 | Patrick Peltier | DENTAL IMPLANT. |
US5205746A (en) * | 1990-01-11 | 1993-04-27 | Societe De Fabrication De Materiel Orthopedique - Sofamor | Surgical implant for oral and maxillofacial implantology |
DE59101624D1 (en) * | 1990-01-15 | 1994-06-23 | Friatec Keramik Kunststoff | Dental implant. |
US5071350A (en) * | 1990-03-21 | 1991-12-10 | Core-Vent Corporation | Tiltable, adjustable, insert for a dental implant |
US5209666A (en) * | 1990-05-15 | 1993-05-11 | Calcitek, Inc. | Endosseous implant system wtih captured screw |
US5135395A (en) * | 1990-07-05 | 1992-08-04 | Marlin Gerald M | Implant collar and post system |
BE1003719A3 (en) * | 1990-07-10 | 1992-05-26 | Ceka Nv | Method for achieving an implant prosthesis and parts used are hereby. |
FR2664808A1 (en) * | 1990-07-23 | 1992-01-24 | Gersberg Eduardo | System of dental implants |
US5209659A (en) * | 1990-09-05 | 1993-05-11 | Impla-Med Incorporated | Method for installing a dental implant |
US5116225A (en) * | 1990-10-17 | 1992-05-26 | Riera Juan C A | Angulated abutment for osseointegrated implants |
US5195891A (en) * | 1990-12-06 | 1993-03-23 | Sulc Josef M | Adjustable dental implant system |
SE470049B (en) * | 1991-03-01 | 1993-11-01 | Nobelpharma Ab | Device at bridge that is individually adapted to dental implants |
SE469159B (en) * | 1991-03-27 | 1993-05-24 | Nobelpharma Ab | CYLINDER INTENDED TO BE USED IN A TEMPORARY, IMPLANT DENTAL DENTAL / DENTAL PROTEIN |
SE468154B (en) * | 1991-08-27 | 1992-11-16 | Nobelpharma Ab | SCREW SIZE TITAN MOUNTING FOR PERMANENT ANCHORING IN BONE TISSUE. |
US5221204A (en) * | 1991-09-23 | 1993-06-22 | Kruger Bernard M | Dental implant product and method of making |
JPH071133Y2 (en) * | 1991-12-06 | 1995-01-18 | 眞一 菅 | Dental implant |
US5197881A (en) * | 1991-12-30 | 1993-03-30 | Wellesley Research Associates, Inc. | Dental implant system and apparatus |
US5302126A (en) * | 1992-03-19 | 1994-04-12 | Park Dental Research Corp. | Dental implant with adjustable post |
US5232364A (en) * | 1992-08-31 | 1993-08-03 | Rosen David B | Dental crown analog for orthodontic anchorage |
US5246370A (en) * | 1992-11-27 | 1993-09-21 | Coatoam Gary W | Dental implant method |
US5292252A (en) * | 1992-12-14 | 1994-03-08 | Impla-Med, Inc. | Stimulator healing cap |
US5269686A (en) * | 1993-05-10 | 1993-12-14 | James Robert A | Threaded drivable dental implant |
US5302127A (en) * | 1993-06-01 | 1994-04-12 | Crisio Jr Raymond A | Dental implant stress stabilizer |
-
1994
- 1994-08-09 US US08/288,278 patent/US5527183A/en not_active Expired - Fee Related
-
1995
- 1995-03-29 EP EP95302105A patent/EP0696445A1/en not_active Ceased
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4270905A (en) * | 1979-02-21 | 1981-06-02 | Mohammed M Hamdi A | Replacement system for dental and other bone implants |
US4437191A (en) * | 1981-04-03 | 1984-03-20 | Delphi Dental Industries B.V. | Implant of ceramic material |
US4792339A (en) * | 1985-05-23 | 1988-12-20 | Laboratorium Fur Experiementelle Chirurgie, Forschungsinstitut | Self-locking stemmed component for a joint endo-prosthesis |
DE3811498A1 (en) * | 1988-04-06 | 1989-10-26 | Witzel Ulrich | Dental jaw implant |
US5222983A (en) * | 1990-09-13 | 1993-06-29 | Thera Patent Gmbh & Co. | Implantable prosthesis |
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2005030081A1 (en) * | 2003-10-01 | 2005-04-07 | Nobel Biocare Ab (Publ) | Implant arrangement with an internal socket for a turning tool |
US10231804B2 (en) | 2003-10-01 | 2019-03-19 | Nobel Biocare Services Ag | Implant arrangement with an internal socket for a turning tool |
WO2010006740A3 (en) * | 2008-07-14 | 2010-08-26 | Nobel Biocare Services Ag | Compact dental implant |
CN102098977A (en) * | 2008-07-14 | 2011-06-15 | 诺贝尔生物服务公司 | Compact dental implant |
JP2011527917A (en) * | 2008-07-14 | 2011-11-10 | ノベル バイオケア サーヴィシィズ アーゲー | Small dental implants |
US8758012B2 (en) | 2008-07-14 | 2014-06-24 | Nobel Biocare Services Ag | Compact dental implant |
CN102098977B (en) * | 2008-07-14 | 2015-09-30 | 诺贝尔生物服务公司 | Compact dental implant |
AU2009270547B2 (en) * | 2008-07-14 | 2015-11-19 | Nobel Biocare Services Ag | Compact dental implant |
EP2328509B1 (en) * | 2008-07-14 | 2019-10-30 | Nobel Biocare Services AG | Compact dental implant |
Also Published As
Publication number | Publication date |
---|---|
US5527183A (en) | 1996-06-18 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US5527183A (en) | Endosseous implant system | |
EP0376944B1 (en) | A tool for a prosthetic part | |
US5000686A (en) | Dental implant fixture | |
US8491302B2 (en) | Dental implant | |
US5199873A (en) | Dental implant | |
JP2627385B2 (en) | Fixing member | |
US5022860A (en) | Ultra-slim dental implant fixtures | |
US6273722B1 (en) | Hybrid press fit-threaded dental implant | |
CA2146679C (en) | Locking plate and bone screw | |
CA2287115C (en) | Allograft bone fixation screw method and apparatus | |
EP2967761B1 (en) | Dental implant with improved prosthetic interface | |
US6887275B2 (en) | Maxillofacial anchoring system for alveolar and small bone skeletal distraction | |
AU656904B2 (en) | A device for tooth implantation comprising a locking screw | |
US6276938B1 (en) | Method and arrangement for executing a cemented superstructure and also distance member and set of distance members | |
US20080145819A1 (en) | Screw-in Enossal Dental Implant | |
US8771285B2 (en) | Drive tool for orthopedic screws | |
US20090298014A1 (en) | Dental Implant | |
US20090305191A1 (en) | Failsafe Installation Tool For Dental Implants | |
JP2014531919A (en) | Acetabular connection fixing screw and a composite structure of the acetabular connection fixing screw and an acetabular cup of an artificial hip joint | |
DE10231743A1 (en) | Screw-in conical enossal dental implant with self-cutting thread arrangement has hole in top part self-centering bottom part | |
CA2286752C (en) | Implant system | |
US20100143865A1 (en) | Instrument for removing a screw stump of a connecting screw of a tooth implant | |
EP0819410A1 (en) | Dental implant and related milling cutter for implant seating | |
CA2286616C (en) | Implant system | |
EP3659544A1 (en) | Connection between dental implants and prosthetic devices |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU MC NL PT SE |
|
AX | Request for extension of the european patent |
Free format text: LT PAYMENT 950407;SI PAYMENT 950407 |
|
RAX | Requested extension states of the european patent have changed |
Free format text: LT PAYMENT 950407;SI PAYMENT 950407 |
|
17P | Request for examination filed |
Effective date: 19960704 |
|
17Q | First examination report despatched |
Effective date: 19981110 |
|
GRAG | Despatch of communication of intention to grant |
Free format text: ORIGINAL CODE: EPIDOS AGRA |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: THE APPLICATION HAS BEEN REFUSED |
|
18R | Application refused |
Effective date: 20000910 |